Blood processing filter

ABSTRACT

A flexible blood filter allowing smooth flow of a liquid and being excellent in separation resistance, pressure resistance and centrifugation resistance. The blood processing filter, includes a first filter element for removing aggregates from blood, a second filter element for removing leukocytes provided in the downstream of the first filter element, and a third filter element having gas permeability of 3 to 40 cc/cm2/sec per thickness of 1 cm provided between the second filter element and the outlet port. The filter contains a seal zone at a peripheral section which contains five layers including a layer of molten material and layers of molten material mixed with filter element material.

TECHNICAL FIELD

The present invention relates to a blood processing filter for removingundesirable components such as aggregate and leukocytes from blood. Inparticular, the present invention relates to a precise and disposableblood processing filter for removing micro aggregate and leukocyteswhich may cause side effects from whole blood preparations, erythrocytepreparations, thrombocyte preparations, blood plasma preparations, andthe like for blood transfusion.

BACKGROUND ART

Whole blood collected from a donor is used for transfusion, as is, onlyin rare cases, but is commonly separated into components, such as anerythrocyte preparation, thrombocyte preparation, blood plasmapreparation, and the like to be stored for transfusion. Since microaggregate and leukocytes included in these blood preparations causevarious side effects during blood transfusion, there have beenincreasing occasions wherein these undesirable components are removedbefore blood transfusion. The need for leukocyte removal has widely beenrecognized particularly in recent years. Removal of leukocytes from allkinds of blood preparations for blood transfusion before using fortransfusion has been legislated in some European countries.

The most common method of removing leukocytes from blood preparations isby processing blood preparations using a leukocyte removing filter.Conventionally, blood preparations have been processed using a leukocyteremoving filter in many cases at the bedside when blood transfusion isperformed. In recent years, however, to improve quality control ofleukocyte-free preparations and efficiency of leukocyte removaloperations, it is more common to process the blood preparations in bloodcenters before storing the blood preparations.

A blood collection-separation set, typically consisting of two to fourflexible bags, a tube connecting these bags, an anticoagulant, anerythrocyte preservation solution, a blood-collecting needle, and thelike has been used for collecting blood from a donor, separating theblood into several blood components, and storing the blood components. Asystem in which a leukocyte removing filter is incorporated into such ablood collection-separation set has been widely used as an optimumsystem for the above-mentioned pre-storage leukocyte removal. Such asystem is called a closed system or an integrated system and the like.Such a system is disclosed in JPA 1-320064, WO 92/20428, and the like.

Conventionally, a filter made from nonwoven fabric or porous filterelements packed in a hard container of polycarbonate or the like hasbeen widely used as a leukocyte removing filter. However, because thecontainer used in such a filter d, International Publication NumberW098/51799oes not have gas permeability, it has been difficult to use avapor sterilization method, which is a widely accepted sterilizationmethod in blood collection-separation sets. In a closed system,leukocytes are first removed from the whole blood preparation aftercollecting the blood. Then, after the leukocyte removing filter isseparated, the leukocyte-free blood is centrifuged for separation intovarious components. In another type of closed system, the whole blood isfirst centrifuged to be divided into various components, and then theleukocytes are removed. In the latter system, the leukocyte removingfilter is also centrifuged together with the blood collection-separationset. In this instance, a hard container may damage bags and tubes, orthe container itself may not withstand the stress and may collapseduring centrifugation.

To solve this problem, flexible leukocyte removing filters, in which thecontainer is made of the same or a similar material having superiorflexibility and high vapor permeability as used for the bags of theblood collection-separation set, have been developed.

These filters are broadly classified into the type in which the filterelements are welded to a sheet-like flexible frame, which is then weldedto a housing material (EP 0 526 678, JPA11-216179) and the type in whichthe flexible container is directly welded to the filter elements (JPA7-267871, WO 95/17236).

The former type may be hereinafter called the frame welding type and thelatter may be called the container welding type.

When processing blood in these types of leukocyte removing filters, thebag containing a blood preparation to be processed, connected to theblood inlet port of the filter via a tube, is placed at a height 20-100cm higher than the filter to allow the blood preparation to pass throughthe filter by action of gravity. After filtration, the blood preparationis stored in a collection bag connected to the blood outlet port of thefilter via a tube. During filtration, a pressure loss is caused due tothe resistance of the filter element, whereby the pressure in the spaceon the inlet side of the filter is maintained positive. In the case ofthe filter attached to a flexible container, the flexibility of thecontainer itself makes the container swell like a balloon due to thepositive pressure, thereby pressing the filter element against theoutlet port side container. Specifically, a force acting to separate thefilter element from the container or the sheet-like frame is alwaysapplied to the joining sections of these parts.

In the case of centrifuging the leukocyte removing filter together withthe blood collection-separation set, a force acting to separate thefilter element from the sheet-like frame or the flexible container mayalso be applied to the joining sections of these parts. As an example,the centrifuge operation using a one-liter-cylindrical centrifuge cup,which is typically employed in the United States and other countries,will be described. A hypothetical system consisting of a blood bag madeof soft polyvinyl chloride containing 570 ml of a whole bloodpreparation treated for anti-coagulation, a blood processing filter, abag made of soft polyvinyl chloride containing about 100 ml of anerythrocyte preservation solution, an empty bag for transferringplatelet-rich plasma after centrifugation, and an empty bag to store theblood after processing with the blood processing filter arranged in thiscentrifuge cup in that order to be centrifuged will be discussed. Tubesmade of soft polyvinyl chloride to connect the bags to the filter areappropriately arranged between the bags and the filter. The bags and thefilter are pressed to the bottom of the centrifuge cup due to thecentrifugal force. The bag containing the whole blood preparation andthe bag containing an erythrocyte preservation solution are deformedcausing them to swell due to the centrifugal force. As a result, theflexible blood processing filter placed between the two blood bags maybe crushed by the blood bags or may be deformed into a configurationconforming to the blood bags. Although the mechanism differs from theabove case in which the container swells like a balloon, as a result,the same force acting to separate the filter element from the sheet-likeframe or the flexible container is applied.

The soft polyvinyl chloride and polyolefin, widely used as materials forcontainers or frames, exhibit only slight adhesion to the materialspopularly used for filter elements such as polyester fibers andpolyurethane porous materials. For these reasons, the joining parts havea problem of being easily separated by a comparatively small force.However, the above-mentioned prior art documents, including EP 0 526678, Japanese Patent Application Laid-open Publication No.11-216179,Japanese Patent Application Laid-open Publication No. 7-267871, and WO95/17236, or the like, disclosing flexible filters have neither realizedthis problem nor described the methods of overcoming the problem.

As a matter of fact, commercially available frame attachment typefilters do not necessarily have sufficient resistance to the forceacting to separate the joining parts of the filter element and theframe. These filters have a risk of invalidating filtration due todetachment of the filter element from the frame during use.

Although there are few commercially available container welding typefilters, such filters also have a risk of container breakage or leakingdue to the same reasons of separating the filter element from thecontainer during use.

Beside the usual filter operation utilizing gravity, the filter may becompulsory primed with blood by pressing or squeezing the bag containingthe blood preparation to be filtered by hand (hereinafter may be called“squeezing”) or may be operated at a high speed by applying a highpressure using a pump. For these reasons, a filter with superiorresistance to pressure and separation has been desired.

Furthermore, during the common filter operation utilizing gravity, aflexible container swells like a balloon due to the positive pressureapplied to the blood inlet side of the filter as mentioned above. Inthis instance, the internal filter element bends by being pressed towardthe outlet port side container. On the other hand, the space between theoutlet port side container and the filter element tends to move towardthe bag for storing the processed blood, which is located 50-100 cmlower than the filter by being caused to descend due to the weight ofblood in the tube connected to the outlet port. A negative pressure iscreated by this action, whereby the outlet port side flexible containertends to be caused to adhere to the filter element. Specifically, thefilter element is known to closely adhere to the outlet port sidecontainer by the double forces, whereby blood flow is obstructed.

As a means for solving this problem, a method of inserting a softpolyvinyl chloride tube called as “a connecting rod” between the filterelement and outlet port side container to prevent adherence (EP 0526678), a method of inserting a screen made of nit fiber (WO 95/17236), amethod of preventing adhesion by providing irregularities with a depthof 0.2-2 mm on the internal surface of the soft container (JapanesePatent Application Laid-open Publication No. 11-216179), and othermethods have been proposed. However, as described in Japanese PatentApplication Laid-open Publication No. 11-216179, the method of insertinga connecting rod or a screen has been considered to have a risk ofinducing defective welding of the container if the other materials areinserted. Although the method disclosed in Japanese Patent ApplicationLaid-open Publication No. 11-216179 has been proposed as a measure forsolving the problem in the method of inserting a connecting rod or ascreen, the solution of the problem was limited to the case in which asoft container is welded with a flexible sheet-like filter.Specifically, although irregularities on the internal surface of thecontainer do not cause a problem for welding the container material withthe sheet frame material, the irregularities on the internal surface ofthe container may cause defective welding when the container material isdirectly welded with the filter element. Thus, the method was notnecessarily satisfactory.

DISCLOSURE OF THE INVENTION

An object of the present invention is to provide a flexible bloodprocessing filter, in which the blood flow may not be affected when thefilter element is pressed to the outlet port side container due to thepositive pressure on the inlet port side or the outlet port sidecontainer is caused to adhere to the filter element due to the negativepressure on the outlet port side during filtration operation. Anotherobject of the present invention is to provide a flexible bloodprocessing filter with superior pressure resistance, separationresistance, and sufficient strength against the pressure duringfiltration or the stress during centrifugation. Still another object ofthe present invention is to provide a flexible blood processing filterwhich can resist a higher pressure generated by a squeezing operation orrapid filtration using a pump, without causing problems such as leaking,fracture, and separation.

As a result of extensive studies to achieve the above objects, thepresent inventors have found that if a filter element having specificcharacteristics and a specific thickness is disposed in the mostdownstream location in contact with the outlet port side container, theblood flow is not obstructed by a blood processing filter having aflexible container. This finding has led to the completion of thepresent invention. The present inventors have further found that if afilter element having specific characteristics and a specific thicknessis disposed in the most downstream location in contact with the outletport side container, not only the blood flow is not obstructed in eitherthe frame welding type filter or the container welding type filter, butalso the filter exhibits remarkably excellent performance in pressureresistance and separation resistance. More surprisingly, the inventorsof the present invention have found that when such a filter element isused, an excellent blood flow can be maintained even after there isalmost no gravity effect on the inlet port side, by which it is possibleto reduce the recovery time during the period close to the end offiltration operation. These findings have also led to the completion ofthe present invention.

As a result of further investigation on the pressure resistance andseparation resistance, the inventors of the present invention have foundthat if a composite material layer with a specified thickness, in whichpart of the filter element is embedded in the materials of thesheet-like frame or the container in the joining area of the flexiblesheet-like frame or flexible container and filter element, is provided,the filter exhibits excellent separation resistance and fractureresistance. The finding has also led to the completion of the presentinvention.

Specifically, the present invention provides a blood processing filtercomprising a flexible container, which has an inlet port and an outletport, and a sheet-like filter element for removing undesirablecomponents from blood, wherein the blood inlet port is separated fromthe outlet port by the filter element, the sheet-like filter elementcomprises a first filter element for removing aggregate from blood, asecond filter element arranged downstream of the first filter element toremove leukocytes, and a third filter element arranged between thesecond filter element and the outlet port side container to prevent thefilter element from adhering to the outlet port side container andobstructing the flow of blood, wherein the third filter element has agas permeability per 1 cm thickness of 3-40 cc/cm²/sec and a thicknessof 0.04-0.25 cm (such a filter is hereinafter referred to from time totime as three-element filter).

The three-element filter preferably has a seal zone formed byintegrating the section near the periphery of the sheet-like filterelement with the flexible container over its entire circumference. Morepreferably, the three-element filter has a first seal zone formed byintegrating the section near the periphery of the sheet-like filterelement with the flexible container over its entire circumference, asecond seal zone formed by integrating the inlet side flexible containerand the outlet side flexible container over the entire outsidecircumference of the first seal zone, and an unsealed zone disposedbetween the first seal zone and the second seal zone. Such a bloodprocessing filter is hereinafter referred to as a “container weldingtype three-element filter” from time to time. In addition, irrespectiveof the presence or absence of the second seal zone, a seal zone formedby integrating the section near the periphery of the sheet-like filterelement with the flexible container over its entire circumference ishereinafter referred to as “first seal zone” from time to time.

The present invention further provides a three-element blood processingfilter comprising at least one flexible sheet-like frame between theflexible container and the sheet-like filter element, wherein the inletport is separated from the outlet port by the filter element and the atleast one sheet-like frame.

The blood processing filter preferably has a first seal zone formed byjoining the entire circumference of the section near the periphery ofthe sheet-like filter element and at least one sheet-like frame, and asecond seal zone formed by integrating the inlet side flexiblecontainer, at least one sheet-like frame, and the outlet side flexiblecontainer over the entire outside circumference of the first seal zone.Such a blood processing filter is hereinafter referred to as a “framewelding type three-element filter” from time to time.

In a further aspect, the present invention provides a blood processingfilter comprising a flexible container, which has an inlet port and anoutlet port, and a sheet-like filter element for removing undesirablecomponents from blood, wherein the blood inlet port is separated fromthe outlet port by the filter element, a seal zone is formed byintegrating the section near the periphery of the sheet-likefilter-element with the flexible container over its entirecircumference, the cross-section of the seal zone comprises at leastfive layers from the blood inlet side to the outlet side, that is, alayer consisting only of the inlet side flexible container material, aninlet port side composite material layer wherein the inlet side flexiblecontainer material is mixed with the filter element material, a layerconsisting only of the filter element material, an outlet port sidecomposite material layer wherein the outlet port side flexible containermaterial is mixed with the filter element material, and a layerconsisting only of the outlet port side flexible container materialwherein both the inlet port side composite material layer and the outletport side composite material layer have a thickness between 0.15 mm and0.4 mm. Such a blood processing filter is hereinafter referred to as a“container welding type composite layer filter” from time to time.

The present invention further provides a blood processing filter havinga composite material layer comprising at least one flexible sheet-likeframe between the inlet port side flexible container and/or the outletport side flexible container and the sheet-like filter element whereinthe blood inlet port is separated from the outlet port by the filterelement and at least one sheet-like frame, and the blood processingfilter has a first seal zone formed by joining the entire circumferenceof the section near the periphery of the sheet-like filter element andat least one sheet-like frame, and a second seal zone formed byintegrating the inlet side flexible container, the outlet side flexiblecontainer, and at least one sheet-like frame over the entire outsidecircumference of the first seal zone wherein the cross-section of thefirst seal zone has at least three layers, which are a layer consistingonly of the sheet-like frame material, a composite material layerwherein the sheet-like frame material is mixed with the filter elementmaterial, and a layer consisting only of the filter element material,and the composite material layer has a thickness between 0.15 mm and 0.4mm. Such a blood processing filter is hereinafter referred to as a“frame welding type composite layer filter” from time to time.

In the above-mentioned container welding type composite layer filter andthe frame welding type composite layer filter, the sheet-like filterelement preferably comprises a first filter element for removingaggregate from blood, a second filter element arranged downstream of thefirst filter element to remove leukocytes, and a third filter elementarranged between the second filter element and the outlet port sidecontainer, wherein the third filter element has a thickness of 0.04-0.25cm and a gas permeability of 3-40 cc/cm²/sec per thickness of 1 cm.

The container welding type three-element filter and container weldingtype composite layer filter are collectively referred to as containerwelding type blood processing filters from time to time. Similarly, theframe welding type three-element filter and frame welding type compositelayer filter are collectively referred to as a frame welding type bloodprocessing filter from time to time. In addition, the container weldingtype composite layer filter and frame welding type composite layerfilter are collectively referred to as a composite layer filter fromtime to time.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic sectional view of a container welding type bloodprocessing filter of the present invention.

FIG. 2 is a schematic sectional view of the frame welding type bloodprocessing filter of the present invention.

FIG. 3 is a schematic sectional view of the first seal region of thepresent invention.

BEST MODE FOR CARRYING OUT THE INVENTION

The present invention will be described in more detail below.

The entire shape of the blood processing filter of the present inventionmay be rectangular, lozenge-shaped, disk-like, or oval. A rectangular orlozenge-shaped filter is preferable for decreasing loss of materialswhen manufacturing the filters. In this specification, a squareconfiguration is included in the rectangular configuration.

The flexible container used in the present invention is preferablyformed from a flexible sheet-like or a cylindrical formed object of asynthetic resin, preferably a thermoplastic resin.

The inlet port and outlet port for blood maybe integrally formed withthe flexible container when the container is formed by injection moldingor the like. Alternatively, holes or slits maybe provided in anextrusion-molded sheet-like film or cylindrical film, and then, theholes or slits may be liquid-tightly and communicatingly joined withparts for the inlet port and outlet port, made by injection molding orextrusion molding, by a known method such as a method of using anadhesive, heat sealing, or high frequency welding. The latter method ismore preferable because of the rare chance of the container beingdeformed during sterilization using vapor and ease of manufacturing.

When the filter has a sheet-like frame, tubular sections that canfunction as an inlet port and an outlet port for blood may be insertedand bonded between the sheet-like or cylindrical film and the sheet-likeframe.

When the parts for the inlet port and outlet port including tubularsections are liquid-tightly attached to the sheet-like or cylindricalfilm, the material of the parts for the inlet port and outlet port maybe either the same as or different from the material for the sheet-likeor cylindrical film. When different materials are used, there are nospecific limitations to the types of the materials in as much as theinlet and outlet ports can be liquid-tightly joined with the sheet-likeor cylindrical film and can be handled without a problem. However, whenthese parts are connected using a means suitable for mass productionsuch as heat sealing or high frequency welding, a material havingthermal and electrical properties similar to the sheet-like orcylindrical film is preferable.

When two materials, both having a comparatively high dielectric constantsuch as soft polyvinyl chloride, are used, high frequency welding cansuitably join these materials. When two materials, both having acomparatively low dielectric constant and comparatively low meltingpoint such as polyolefin, are used, heat sealing can suitably join thesematerials.

The flexible container and frame-shaped sheet of the present inventionare preferably made of materials having thermal and electricalproperties similar to the material for the filter element. For example,thermoplastic elastomers such as soft polyvinyl chloride, polyurethane,ethylene-vinyl acetate copolymer, polyolefin such as polyethylene andpolypropylene, hydrogenated styrene-butadiene-styrene copolymer,styrene-isoprene-styrene copolymer, and hydrogenated products thereof,mixtures of the thermoplastic elastomer and a softening agent such aspolyolefin and ethylene-ethyl acrylate, and the like can be given aspreferable materials. Of these, preferable materials are thermoplasticelastomers such as soft polyvinyl chloride, polyurethane, ethylene-vinylacetate copolymer, polyolefin, and mixtures the thermoplastic elastomerscontaining these mixtures as a major component, with particularlypreferable materials being soft polyvinyl chloride and polyolefin.

The sheet-like filter elements used for the three-element filter of thepresent invention comprises a first filter element for removingaggregate from blood, a second filter element arranged downstream of thefirst filter element to remove leukocytes, and a third filter elementarranged between the second filter element and the outlet port sidecontainer. The third filter element has a gas permeability of 3-40cc/cm²/sec per thickness of 1 cm and a thickness of 0.04-0.25 cm. Thesheet-like filter element in a composite layer filter need notnecessarily comprise the first, second, and third filter elements, butpreferably comprises the first and third filter elements from theviewpoint of ease of forming the composite material layer

The gas permeability herein used indicates the amount of permeating air(cc/cm² /second) measured by the test method described in JIS L-1096,6.27.1 A-method (1992 edition) and the gas permeability per thickness of1 cm indicates the value obtained by multiplying the gas permeability bythe thickness (cm) of the third filter element.

The thickness herein used indicates the value determined by measuringthe thickness at 1.5 N using a dial gauge with a measuring piece havinga diameter of 10 mm according to the method defined in JIS B7503 (1992edition). When the third filter element is made of two or morematerials, such as several sheets of nonwoven fabric, woven fabric, andthe like, for example, the gas permeability and thickness for each sheetare measured and then the gas permeability per 1 cm thickness isdetermined. The third filter element of the present invention must havethe gas permeability within the range of 3-40 cc cm²/sec, with a totalthickness being 0.04-0.25 cm. For example, a third filter elementcontaining a filter element having a gas permeability of less than 3cm²/sec or a filter element having a gas permeability of more than 40cm²/sec inserted between the filter elements having a gas permeabilityof 3-40 cc cm²/sec is included in the scope of the present invention.

The gas permeability for one sheet of the third filter element may notbe easily determined by a standard method according to the above testwhen the fiber diameter or the pore diameter of the third filter elementis too large or the thickness of one sheet is too thin. In thisinstance, after determining the gas permeability by laminating severalsheets or by masking a part of the area of the test specimen for whichthe gas permeability is measured, the value for one sheet or for oneunit area can be determined by converting the measured value.

The third filter element allows the blood going to the outlet port afterpassing through the second filter element to flow in the third filterelement in the direction perpendicular to the thickness of the filterelement, even in the case in which the filter element is caused toadhere to the outlet port side container due to the positive pressure onthe filter inlet side and the negative pressure on the filter outletside, whereby the time required for filtration and recovery can beshortened.

In the case in which the gas permeability per 1 cm thickness is lessthan 3 cc/cm²/sec, the above blood flow in the perpendicular directionafter passing through the second filter element cannot be sufficientlyachieved, resulting in retardation of filtration and, in particular,recovery. If the gas permeability per 1 cm thickness is more than 40cc/cm²/sec, the pressure resistance and separation resistance may beinsufficient.

A more preferable range for the gas permeability per 1 cm thickness is3.5-10 cc/cm²/sec, with an optimum range being 4-9 cc/cm²/sec.

If the thickness of the third filter element is less than 0.04 cm, theblood flow in the perpendicular direction becomes insufficient,resulting in retardation of filtration time. When the thickness of thethird filter element is more than 0.25 cm, on the other hand, the effectof decreasing the filtration time and recovery time cannot be obtainedany more. The third filter element increases the resistance to the bloodflow, which not only gives rise to retardation of the filtration timeand recovery time on the contrary, but also increases loss of the bloodpreparations.

A more preferable thickness of the third filter element is 0.05-0.20 cm,with the range of 0.06-0.15 cm being ideal.

Known filter media, such as porous fiber materials including nonwovenfabric, woven fabric, and mesh, as well as porous materials havingthree-dimensional braided continuous pores can be used as the filterelement in the present invention. The materials for such filter mediainclude polypropylene, polyethylene, styrene-isobutylene-styrenecopolymer, polyurethane, polyester, and the like.

Usually, filter media with different fiber diameter and pore diameterare used for the first filter element and the second filter element. Forexample, a filter material with a fiber diameter between several μm toseveral tens of μm is arranged in the inlet side as a first filterelement for removing aggregate, a filter material with a fiber diameterof 0.3-3.0 μm is arranged next as a second filter element for removingleukocytes, and a third filter is laminated downstream of the secondfilter element.

Each of the first, second, and third filter elements may be formedfurther from two or more different filter elements. In this instance,the first and second filter elements are preferably arranged so that thefiber diameter increases stepwise or continuously from the section ofthe second filter element with the smallest fiber diameter toward theinlet port and the outlet port.

In the same manner, when porous materials having three-dimensionalbraided continuous pores are used as the first and second filterelements, these filter elements are preferably arranged so that the porediameter increases stepwise or continuously from the section of thesecond filter element with the smallest pore diameter toward the inletport and the outlet port.

In the same manner, the third filter element is preferably arranged sothat the fluid permeability per 1 cm thickness increases either stepwiseor continuously from the section in contact with the second filterelement toward the section in contact with the outlet port sidecontainer.

The first seal zone in the container welding type filter and the firstseal zone in the frame welding type filter of the present invention(hereinafter may be referred to collectively as “first seal zone”) canbe formed by joining the flexible container or the frame-like sheet withthe section near the periphery of the filter element by internal weldingusing a high frequency welding method or a supersonic wave weldingmethod or by external welding with heat. The high frequency weldingmethod is preferably used when the container or the frame-like sheet andthe filter element are made from materials with a comparatively highdielectric constant, and the heat sealing is preferably used when eitherone material has a low dielectric constant or both materials have a lowmelting point.

The first seal zone may be formed either in the outermost periphery ofthe filter element or in a point slightly inside the outermostperiphery, for instance, a point several mm inside the periphery. Thelatter case is more preferable because the several mm margin of thefilter element, which is left unsealed outside the first seal zone,ensures safe and sure sealing.

It is unnecessary for the entire filter elements to be integral with theflexible container or the sheet-like frame in the first seal zone. Inthe three filter elements of the present invention, it is desirable thatat least the second filter element, a part of the first filter elementcontacting the second filter element, and a part of the third filterelement contacting the second filter element be integral. It is morepreferable that all the filter elements be integral. The first filterelement and third filter element, which are to be integrally formed,have a thickness of preferably 50-1,000%, more preferably 70-500%, andstill more preferably 100-250% of the thickness of the container or thesheet-like frame to be integrated. Although the thickness of thecontainer or the sheet-like frame should be defined as the thickness forthe section corresponding to the first seal zone before joining, it ispossible to replace such a thickness corresponding to the first sealzone with the thickness of the container material or the sheet-likeframe material adjacent to, but at inner side from, the seal zone afterjoining.

In addition, in the container welding type composite layer filter of thepresent invention, the cross-section of the first seal zone comprises atleast five layers from the blood inlet side to the outlet side, that is,a layer consisting only of the inlet port side container material, aninlet side composite material layer wherein the inlet port sidecontainer material is mixed with the filter element material, a layerconsisting only of the filter element material, an outlet side compositematerial layer wherein the outlet port side container material is mixedwith the filter element material, and a layer consisting only of theoutlet port side container material or the sheet-like frame. Both theinlet side composite material layer and the outlet side compositematerial layer have a thickness of 0.15-0.4 mm.

The frame welding type composite layer filter has a cross-section of thefirst seal zone comprising at least 3 layers, that is, a layerconsisting only of the sheet-like frame material, a composite materiallayer wherein the sheet-like frame material is mixed with the filterelement material, and a layer consisting only of the filter elementmaterial. The composite material layer has a thickness of 0.15-0.4 mm.When a sheet-like frame is joined with a filter element, the sheet-likeframe may be located either on the upstream side or on the downstreamside of the filter element. In the former case, at least three layersare observed in the cross-section of the seal zone, which are, from theblood inlet side to the outlet side; a layer consisting only of thesheet-like frame material, a composite material layer wherein thesheet-like frame material is mixed with the filter element material, anda layer consisting only of the filter element material. In the lattercase, at least three layers are observed, which are, from the bloodinlet side to the outlet side, a layer consisting only of the filterelement material, a composite material layer wherein the sheet-likeframe material is mixed with the filter element material, and a layerconsisting only of the sheet-like frame material.

It is possible to form a first seal zone consisting of five layers,wherein the filter elements are sandwiched by two sheet-like frames. Thefive layers are, from the blood inlet side to the outlet side, a layerconsisting only of the inlet side sheet-like frame material, a compositematerial layer wherein the inlet side sheet-like frame material is mixedwith the filter element material, a layer consisting only of the filterelement material, a composite material layer wherein the outlet sidesheet-like frame material is mixed with the filter element material, anda layer consisting only of the outlet side sheet-like frame material.

In this case, either the sheet-like frame on the inlet side or thesheet-like frame on the outlet side must be integrated with the flexiblematerial on both the inlet side and the outlet side, thereby forming thesecond seal zone. Since the main stress is applied to the sheet-likeframe side integrated with the container, the thickness of the compositematerial containing the sheet-like frame forming the second seal zoneand the filter element as major components must have a thickness of0.15-0.4 mm. This thickness requirement does not necessarily apply tothe composite material containing the sheet-like frame not forming thesecond seal zone and the filter element as major components.

The composite material layer of the present invention is preferably alayer made from of the material of the container or sheet-like frameinvading voids of the filter element material which becomes molten withrelatively difficulty, resulting in a layer in which the former materialembeds the fibrous or porous material of the filter element therein.

The thickness of the composite material layer must be between 0.15 to0.4 mm. If the thickness of the composite material layer is smaller than0.15 mm, sufficient separation resistance and fracture resistance cannotbe obtained.

As mentioned above, soft polyvinyl chloride, polyolefin, and the likewidely used as materials for containers or frames, exhibit only slightadhesion to the materials popularly used for filter elements such aspolyester fibers and polyurethane porous materials.

A process for fabricating the composite material layer and the featureof such a process will now be described for the case of forming acomposite material layer on the inlet port side in container weldingtype filter from the container material of soft polyvinyl chloride andthe first filter element made of polyester fiber using high frequencywelding technology. To join the outlet port side container material withthe filter element and inlet port side container material by means ofhigh frequency welding, these materials are laminated, put into a metalmold for high frequency welding, and pressed at a prescribed pressure.Then, a high frequency current is applied. The soft polyvinyl chlorideheated by the high frequency wave becomes softened and molten andinvades voids of fibers in the first filter element by the pressure fromthe metal mold. In this instance, the first filter element is notsufficiently heated to a temperature to cause the fibers to be comemolten. In addition, since the fiber shave a melting point higher thanthe container material, the fibers are left as is without becomingmolten. The container material invades the fiber voids, resulting in acomposite material layer, in which the fibers are embedded by thematerial of the container. On the other hand, an inner filter element,for example, the second filter element in the present invention, tendsto become heated from around the center in terms of the thickness of theentire filter element. As a result, the filter element is heated by thehigh frequency wave to the melting point earlier than the time when thecontainer material invades from the inlet side and becomes molten to theextent that the molten material reaches the composite material. As aresult of formation of the composite material layer also on the outletside in the same manner, a first seal zone consisting of five layers isultimately formed.

The thickness of the composite material layer is determined by thebalance of the invasion speed of the container material and the meltingspeed of the filter element. However, since the invasion speed of thecontainer material is affected by the different fiber diameters and poresizes of the filter element, the thickness of the composite materiallayer is determined as a result of extremely complicated phenomenainvolving various factors other than the high frequency weldingconditions when two or more filter elements with different fiberdiameters and pore sizes are used. Therefore, it is preferable todetermine the conditions for forming a composite material layer with adesired thickness by previous experiments.

The first seal zone can be formed from a sheet-like frame material and afilter element material in the same manner also in the case of the framewelding type filter.

In the composite material layer formed according to the above-describedprocess, when the container material or the sheet-like frame materialencompassing fibers do no have adhesion with the fibers, it is importantfor the filter element to be sufficiently engaged with the containermaterial or the sheet-like frame material to resist the force acting toseparate the container or the sheet-like frame from the filter element.Such engaging strength is thought to have a certain correlation with thethickness of the composite material layer. Therefore, at the beginningof examination of the present invention, it was anticipated that thethicker the composite material layer, the stronger the engagingstrength. Unexpectedly, however, it was found that some compositematerial layers with a thickness exceeding 0.4 mm have inferior pressureresistance in some cases, that is, fluctuated pressure resistance andseparation resistance. The thickness of the composite material layertherefore must be 0.4 mm or less.

A more preferable thickness of the composite material layer is 0.18-0.35mm, with the range of 0.23-0.33 mm being ideal. In addition, thethickness of the outlet port side composite material layer is preferablyas close as the thickness of the inlet port side composite materiallayer. Specifically, the thickness difference is preferably within 0.1mm, and more preferably within 0.05 mm.

The invasion speed of the container material may be larger than themelting speed of the filter element depending on the selection of theconstruction of the filter element and high frequency weldingconditions. In such a case, the entire container material may invade thefirst filter element before the second filter element melts and expands.The fiber diameter and pore size of the second filter element forremoving leukocytes are usually smaller than those of the first filterelement by far. The material for the container cannot easily invade suchfibers and pores even in the molten state. As a result, layersconsisting only of the container material, which are considered to havebeen formed from the invaded container material, may be observed betweenthe first filter element and the second filter element. In thisinstance, the container material and the second filter element, whichare not inherently adhesive, come into contact along a surface ,resulting in decreased pressure resistance and separation resistance.

Therefore, fibers of the first filter element, of which one half theamount is embedded in the container material and the other half ismolten with the second filter element and embedded therein, arepreferably present in the interface of the composite material layer andthe layer consisting only of the filter element. In such an instance, aboundary line between the composite material layer and the layerconsisting only of the filter element exhibits a complicatedmicrostructure (hereinafter may be referred to as “anchor structure”) inthe cross-section of the first seal zone. Although an example of theanchor structure in the first filter element formed from fibers has beendescribed above, such an anchor structure may be formed in the secondfilter element, the third filter element, or the filter element formedfrom porous material having three-dimensional braided continuous pores.

The thickness of the composite material layer can be determined byvarious methods such as a method of previously specifying a point in thefirst seal zone at which the layers are most likely to separate andcutting the section including that point to inspect the reflectionelectronic image using a scanning electron microscope, a method ofemploying both the inspection using a scanning electron microscopetogether with EDX analysis (energy dispersive X-ray analysis), a methodof applying an etching treatment, for example, by coating a solventwhich selectively dissolves one of the materials forming the compositematerial layer, followed by inspection using a scanning electronmicroscope or a laser microscope, and the like. The method of observingthe reflection electronic image using a scanning electron microscope issuitable for inspecting the anchor structure. A simple method ofspecifying the easily separated point in the container welding typefilter is closing the blood outlet port with a clamp and feedingpressurized air from the blood inlet port until the container fractures(this method may be hereinafter referred to as “burst test”).

The burst test for the frame welding type filter is carried out afterforming a structure similar to the container welding type filter byjoining the sheet-like frame with a sheet-like material having aconfiguration the same as or similar to the frame. Alternatively, amethod of measuring the separation strength at each section of the firstseal zone using an Instron-type all-purpose tensile compression testermay be employed for the burst test for the frame welding type filter.The first seal zone usually has a width of several mm. If the thicknessof the composite material layer differs within this range of width, thethickness at several points wherein the anchor structure is observed ismeasured and the average of the measured values is employed. When it isdifficult to specify the anchor structure, the thickness of the pointhaving the maximum thickness is regarded as the thickness of thecomposite material layer.

The width of the first seal zone is preferably 1-6 mm, more preferably2-5 mm, and still more preferably 3-4 mm. If less than 1 mm, the joinedpart becomes like a line, which has a risk of failing to exhibitsufficient sealing performance when subjected to high-pressure vaporsterilization or roughly handled. The first seal zone with a widthexceeding 6 mm, which tends to become hardened by high frequencywelding, heat sealing, or the like, becomes excessively wide, wherebypart of the characteristics as a flexible container may be lost, thatis, not preferable.

The sheet-like frame used for the frame welding type blood processingfilter of the present invention indicates a frame-shaped materialprepared by deleting the part corresponding to the effective filteringsection inside the first seal zone from a flexible sheet-like formedmaterial by means of cutting or punching. The sheet-like frame formed byinjection molding into a frame-shaped product may also be included. Theterm “frame-shaped” herein used is not limited to a shape with arectangular contour, but includes a shape produced from a lozenge-shapedobject, a circular object, or oval object by removing the inner portionand leaving the periphery, according to the shape of the flexiblecontainer or the effective filtration part.

The sheet-like frame must be provided on either the blood inlet side oroutlet side, but may be provided on both the inlet and outlet sides. Theportion near the inner periphery of the sheet-like frame must beintegrated with the portion near the outer periphery of the filterelement to form the first seal zone. In addition, the outer periphery ofthe frame must be integrated with the inlet port side container and theoutlet port side container to form the second seal zone. However, whenthe frame is provided on both the inlet side and outlet side, it is onlynecessary for the frame to be integrated with either the inlet port sidecontainer or the outlet port side container to form the second sealzone, thereby isolating the inlet port from the outlet port by thefilter element and the sheet-like frame. It is thus unnecessary for theframe to be integrated with both the inlet port side container and theoutlet port side container to form the second seal zone. The filterelement is indirectly joined with the container via the sheet-likeframe, whereby an upstream chamber surrounded by the uppermost part ofthe filter element, the inlet port side container, and the sheet-likeframe, to which the blood inlet port is connected, and a downstreamchamber surrounded by the lowermost part of the filter element, theoutlet port side container, and the sheet-like frame, to which the bloodoutlet port is connected are formed. In this manner, a filter with theblood inlet port being separated from the outlet port by the filterelement and the sheet-like frame is formed.

A known method such as high frequency welding, internal welding bysupersonic wave welding, external welding by heat sealing, adhesionusing a solvent, or the like can be used for forming a second seal zone.The high frequency welding is preferably used when the flexiblecontainer is made from a material with a comparatively high dielectricconstant, and the heat sealing is preferably used when the material hasa low dielectric constant and a low melting point.

The width of the second seal zone is preferably 1-10 mm, and morepreferably 2-5 mm. If less than 1 mm, sealing performance may not berelied upon. A width of 10 mm or less is desirable because anunnecessarily wide weld increases the amount of material used.

A second seal zone, formed by integrating the inlet side flexiblecontainer material with the outlet side flexible container material overtheir entire circumference, may be provided outside the seal zone in thecontainer welding type filter of the present invention. In this case,for the sake of distinguishing from the second seal zone, the seal zoneformed by integrating the container material with the filter materialmay be called a first seal zone of the container welding type filter.Since the second seal zone can avoid the risk of exposing the medicalworkers to the danger of infection or prevent blood preparations frombeing contaminated with miscellaneous bacteria in the case the firstseal zone is broken to leak due to operational mistakes or roughhandling, stress of centrifugal operation, or as such during filteringoperation, it is preferable also for the container welding type filterto be provided with a second seal zone.

Still more preferably, the container welding type filter is providedwith an unsealed zone between the first seal zone and the second sealzone. In this instance, the width of the unsealed zone is preferably1-30 mm. The unsealed zone makes it easy to detect leaking occurring inthe first seal zone.

The flexible container of the present invention may be formed eitherfrom a film-like sheet or a cylindrical sheet. When the blood processingfilter is formed from a film-like sheet, a filter element may besandwiched between two film sheets. It is also possible to fold a filmsheet and place the filter element in the folded film sheet.

When a first seal zone in the container welding type filter is formedfrom a folded film sheet and a filter element sandwiched in the foldedfilm sheet, it is unnecessary to form the second seal zone over theentire circumference of the filter. The above object can be achieved bysealing only the open three sides. This feature is also within the scopeof the present invention. When the first seal zone is formed in thecontainer welding type filter by placing the filter element inside acylindrical film, it is unnecessary to form the second seal zone overthe entire circumference of the filter, but the above object can beachieved by sealing only the open two sides. This feature is also withinthe scope of the present invention.

One embodiment of the blood processing filter of the present inventionis shown in FIG. 1, which should not be construed as limiting thepresent invention.

FIG. 1 is a schematic sectional view of a container welding type bloodprocessing filter of the present invention. In a blood processing filter(m) comprising an inlet side flexible container (b) made from a sheet ofresin equipped with a blood inlet port (a), an outlet side flexiblecontainer (d) made from a sheet of resin equipped with a blood outletport (e), and a filter element (c) for removing undesirable componentsfrom blood, wherein the blood inlet port (a) and outlet port (e) areseparated by the filter element (c), the filter element (c) has a firstseal zone (f), which is disposed between the inlet side flexiblecontainer and the outlet side flexible container, integrated with theflexible container with the section near the periphery being welded withthe flexible container over its entire circumference, and, outside thefirst seal zone, a second seal zone (i), integrated by welding the inletside flexible container and outlet side flexible container. The firstseal zone (f) is formed slightly inside the outermost periphery of thefilter element (c). There is a filter element (g) left unsealed in anunsealed zone (h) at the outside of the first seal zone (f). The filterelement (c) consists of a first filter element (j), a second filterelement (k) and a third filter element (l).

FIG. 2 is a schematic sectional view of a frame attachment type bloodprocessing filter. A blood processing filter having a sheet-like framedisposed on both the inlet side and the outlet side, with only theoutlet side sheet-like frame being integrated with the container in thesecond seal zone, is shown in FIG. 2. In FIG. 2, the same parts as thoseshown in FIG. 1 are indicated by the same symbols.

In the blood processing filter comprising a blood inlet port (a), theblood outlet port (e), an inlet side flexible container (b), an outletside flexible container (d), a sheet-like filter element (c) forremoving undesirable components from blood, an inlet side flexiblesheet-like frame (o) disposed between the inlet side flexible container(b) and the sheet-like filter element (c), and an outlet side flexiblesheet-like frame (n) disposed between the outlet side flexible container(d) and the sheet-like filter element (c), wherein the blood inlet port(a) and the outlet port (e) are separated by the filter element (c) andthe outlet side flexible sheet-like frame (n), a first seal zone (f) isformed by joining the entire circumference of the section near theperiphery of the sheet-like filter element and the two sheet-likeframes, and a second seal zone (i) is formed by integrating the inletside flexible container, the outlet side sheet-like frame, and theoutlet side flexible container over the entire outside circumference ofthe first seal zone. The first seal zone (f) is formed slightly insidethe outermost periphery of the filter element (c). Outside the firstseal zone (f), there is a filter element (g) left unsealed. In the aboveconfiguration, an upstream chamber (A) encircled by the uppermost partof the filter element (c), the inlet side container (b), and the outletside sheet-like frame (n), to which the blood inlet port (a) isconnected, and a downstream chamber (B) encircled by the lowermost partof the filter element (c), the outlet side container (d), and the outletside sheet-like frame (n), to which the blood outlet port (e) isconnected, are formed whereby a blood processing filter with the bloodinlet port and the outlet port being separated by the filter element andthe outlet side sheet-like frame is formed.

Although the sheets in the first seal zone and the second seal zone areseparately shown in FIG. 2 for ease of understanding, these elements maybe integrally formed by welding in practice.

In addition, although the blood inlet and outlet ports are provided inthe second seal zone in the embodiment shown in FIG. 2, the blood inletand outlet ports for the frame welding type blood processing filter maybe provided directly on the flexible container in the same manner as inFIG. 1.

FIG. 3 schematically shows the cross-section of a test specimen cut fromthe first seal zone of the blood processing filter shown in FIG. 1 orFIG. 2. The cross-section consists of the following five layers: a layer(p) made only of the material for the inlet side container or thesheet-like frame, an inlet side composite layer (q) made of a mixture ofthe material for the inlet side container or the sheet-like frame andthe filter element material, a layer (r) made only of the filter elementmaterial, an outlet side composite layer (s) made of a mixture of thematerial for the outlet side container or the sheet-like frame and thefilter element material, and a layer (t) made only of the material forthe outlet side container or the sheet-like frame. These layers have thefollowing thickness. The layer (p) made only of the material for theinlet side container or the sheet-like frame: 0.15 mm, the inlet sidecomposite layer (q) made of a mixture of the material for the inlet sidecontainer or the sheet-like frame and the filter element material: 0.25mm, the layer (r) made only of the filter element material: 0.9 mm, theoutlet side composite layer (s) made of a mixture of the material forthe outlet side container or the sheet-like frame and the filter elementmaterial: 0.23 mm, and the layer (t) made only of the material for theoutlet side container or the sheet-like frame: 0.16 mm. The totalthickness of the first seal zone is 1.69 mm.

EXAMPLES

The leukocyte removing filter of the present invention will now bedescribed in detail by way of examples, which should not be construed aslimiting the present invention.

(Measuring Method)

(1) Measurement of Recovery Time and Amount of Blood Loss

The blood processing filter of the present invention was disposedbetween a pre-processing blood reservoir and a post-processing bloodrecovery bag. An inlet side tube joined with the pre-processing bloodreservoir was connected to the blood inlet port (a) of the bloodprocessing filter and an outlet side tube joined with thepost-processing blood recovery bag was connected to the blood outletport (e) of the blood processing filter. A tube made of vinyl chloride,having an internal diameter of 3 mm, an external diameter of 4.2 mm, anda length of 50 cm was used for both tubes. A Y-shaped tube was joinedaround the center of both the inlet side tube and the outlet side tube.A bypass tube for joining these Y-shaped tubes was provided. Inaddition, a blood feeding tube for feeding the blood was joined to thepre-processing blood reservoir, thereby forming a system.

After closing the inlet side tube and bypass tube using clamps, 250 ml ahigh concentration solution of cow's erythrocyte, containing CPD(citrate phosphate dextrose) added thereto, was charged to thepre-processing blood reservoir from the blood feed tube. Thereafter, theblood feed tube was separated from the root and the opening left afterthe separation was sealed by heating.

The entire system was suspended and the post-processing blood recoverybag was allowed to stand on a balance. Then, the clamp closing the inletside tube was released to open the tube, thereby starting filtration.Blood in the pre-processing blood reservoir flowed out by gravity,passed through the blood processing filter (m), and was collected in thepost-processing blood recovery bag. During processing of blood, theinlet side of the blood processing filter (m) expanded like a balloondue to the action of gravity.

The pre-processing blood reservoir soon emptied. At this point in time,blood still remained in the blood processing filter (m) expended by theaction of pressure. The remaining blood was collected in thepost-processing blood recovery bag by the action of gravity. The periodof time from the time when the pre-processing blood reservoir hasemptied, through the time when the weight of the post-processing bloodrecovery bag has ceased to increase, until the time the blood remainingin the blood processing filter (m) has been collected is defined asrecovery time.

After the completion of blood collection, a point between the Y-lettertube provided in the outlet side tube and the blood processing filter(m) was closed by a clamp. Then, the clamp that had closed the bypasstube was released while squeezing the post-processing blood recovery bagto push the air in the post-processing blood recovery bag up to thepre-processing blood reservoir. The bypass tube was closed again withthe clamp when all the air in the post-processing blood recovery bag wasevacuated. Then, the clamp between the Y-tube provided in the outletside tube and the blood processing filter (m) was released and thesystem was allowed to stand, whereupon the air which had been pushed upinto the pre-processing blood reservoir flowed in to initiate an airrinse. The amount of blood in the post-processing blood recovery bagincreased by a volume equal to the amount of blood in the inlet sidetube and the blood impregnated in the first filter element (j). Theamount of blood remaining in the blood processing filter (m) and thetube after the air rinse was determined as the difference between theamount of blood before processing and the amount of blood afterprocessing. This amount was defined as the amount of blood loss.

(2) Measurement of Container Strength

The blood processing filter was cut (length: about 20 mm) at two pointsacross the first seal zone using a cutter. A test specimen was producedby cutting inside the first seal zone (an area about 30 mm inside fromthe effective filtering section) with the cutting direction beingparallel to the first seal zone. Using a razor edge, irregularities onthe cross-section of the first seal zone were shaved to make the surfacesmooth. The length of the first seal zone was measured by a three-pointvernier caliper. The average was determined as the length of the firstseal zone.

In this instance, the container and the filter element on the effectivefiltering section side in the container welding type blood processingfilter were left attached without separating. For the system having asecond seal zone, the container was separated in the unsealed zone todetermine the strength only of the first seal zone. The containers onthe inlet side and outlet side in the effective filtering section weresecured using a gripper in the effective filtering section side at thepoint 10 mm from the first seal zone to draw the containers in thevertical direction at a speed of 10 mm/min, thereby applying a forceacting to separate out the first seal zone.

Since there is no sheet-like frame material in an amount sufficient tobe secured on the effective filtering section side by the gripper in thecase of the frame welding type blood processing filter using asheet-like frame, the same material was caused to adhere to theeffective filtering section side of the sheet-like frame. The sameexperiment as above was carried out by grasping this material using thegripper.

In the above test, the maximum force required for the container to becompletely separated was converted into force per unit length (1 mm) ofthe first seal zone (N/mm) using the length of the cut out first sealzone. The values were compared (hereinafter referred to as separationstrength) The separation strength was measured at room temperature (23°C.) using a Universal Testing Machine RTC-1250 manufactured by OrientecCorp.

(3) Method of Measuring Thickness of Composite Material Layer

To inspect the cross-section of the first seal zone, a test specimen wascut out, using a cutter knife, from the effective filtering sectionthrough the second seal zone vertically across the first seal zone.Irregularities on the cross-section of the first seal zone were shavedwith a razor edge to make the surface smooth. A photograph of thespecimen prepared in this manner was taken using a scanning electronmicroscope to inspect the reflection electronic image. The thickness ofthe composite material layer was determined from the photograph. Thethickness was measured at several points along the entire length of thefirst seal zone. The average of the anchor structural area or the valueof the thickest part was used as the thickness of the composite materiallayer.

(4) Burst Test Method

A container welding type filter with the second seal zone cut out orwithout a second seal zone was prepared. The end of the filter elementout side the first seal zone was exposed. After closing the blood outletport with a clamp and joining the tube with the blood inlet port, thefilter was immersed in water. Air under a pressure of 0.08 Mpa was fedfrom the tube to determine the period of time required for the firstseal zone to be separated and for the air to begin to leak. The timethus determined was regarded as the container fracture time.

Since the filter element is brought to a condition as if the filter wereclogged during the burst test of a frame welding type filter using asheet-like frame, the burst test was carried out by causing the filtermade of the same material as the sheet-like frame to adhere to thesheet-like frame on the inlet side of the filter element.

Example 1

A flexible sheet of polyvinyl chloride resin with a size 20 mm larger,both in the length and width, than the outer dimension of the secondseal zone and a thickness of 0.037 cm was prepared. The sheet wasprovided with holes with a diameter equivalent to or larger than theinternal diameter of the blood inlet and outlet ports in locationscorresponding to the inlet and outlet ports when the sheet is caused toadhere to the container. Parts for the blood inlet and outlet portshaving an internal diameter allowing the tube to be sealingly insertedtherein were prepared from apolyvinyl chloride resin by injectionmolding. The parts for the blood inlet and outlet ports were attached tothe holes of the polyvinyl chloride resin sheet by high frequencywelding to obtain a flexible container (b) for the inlet port sideequipped with the blood inlet port (a) and a flexible container (d) forthe outlet port side equipped with the blood outlet port (e).

A laminate of the following sheets of nonwoven polyester fabric wereused as the filter element (c). Four sheets of nonwoven fabric (1) withan average fiber diameter of 12 μm and a density of 30 g/m² was used asthe first filter element (j). As the second filter element (k) a total27 sheets of nonwoven fabric consisting of one sheet of nonwoven fabric(2) with an average fiber diameter of 1.7 μm and a density of 66 g/m²,25 sheets of nonwoven fabric (3) with an average fiber diameter of 1.2μm and a density of 40 g/m², and one sheet of nonwoven fabric (2) werelaminated in that order. As the third filter element (1), six sheets ofnonwoven fabric, each having a thickness of 0.019 cm and a gaspermeability per 1 cm thickness of 4.5 cc/cm²/sec, were laminated toobtain a laminated sheet with a thickness of 0.114 cm. The three filterelements were laminated in that order. The laminated sheet of the threefilter elements obtained as described above was cut into a rectangle of91 mm×74 mm to be used as the filter element (c). The flexiblecontainers (b, d) and the filter element (c) were layered in the orderof the inlet port side flexible container (b), filter element (c), andoutlet port side flexible container (d) and welded by high frequencywelding to form the first seal zone with the dimension of a filteringsection of 75 mm×58 mm and the width (f) of the first seal zone of 3 mm.In forming the first seal zone, the separation strength was previouslytested to determine the high frequency welding conditions under whichthe separation strength becomes maximum when the above filter element(c) was used. A second seal zone was formed 3 mm outside the outermostcircumference of the filter element by combining the inlet port sidecontainer and the outlet port side container by high frequency wieldingto provide a width (i) of 4 mm for the second seal zone. The containermaterial remaining outside the second seal zone was cut and removed.

The blood filter obtained in this manner was inspected according to theabove-mentioned methods of measuring recovery time and the amount ofblood loss to determine the recovery time and the amount of blood loss.In addition, the separation strength was determined according to theabove-mentioned method of measuring the container strength. Each testwas repeated five times to determine the average. The results are shownin Table 1.

Example 2

A filter was prepared in the same manner as in Example 1, except that asa third filter element three sheets of nonwoven fabric, each having athickness of 0.019 cm and a gas permeability per 1 cm thickness of 4.5cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.057 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 3

A filter was prepared in the same manner as in Example 1, except that asa third filter element nine sheets of nonwoven fabric, each having athickness of 0.019 cm and a gas permeability per 1 cm thickness of 4.5cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.171 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 4

A filter was prepared in the same manner as in Example 1, except that asa third filter element 12 sheets of nonwoven fabric, each having athickness of 0.019 cm and a gas permeability per 1 cm thickness of 4.5cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.228 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 5

A filter was prepared in the same manner as in Example 1, except that asa third filter element four sheets of nonwoven fabric, each having athickness of 0.022 cm and a gas permeability per 1 cm thickness of 3.2cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.088 cm. The recovery time, the amount of blood loss, and theseparation strength were determined. The results are shown in Table 1.

Example 6

A filter was prepared in the same manner as in Example 1, except that asa third filter element five sheets of nonwoven fabric, each having athickness of 0.021 cm and a gas permeability per 1 cm thickness of 3.8cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.105 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 7

A filter was prepared in the same manner as in Example 1, except that asa third filter element two sheets of nonwoven fabric, each having athickness of 0.023 cm and a gas permeability per 1 cm thickness of 8.8cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.046 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 8

A filter was prepared in the same manner as in Example 1, except that asa third filter element five sheets of nonwoven fabric, each having athickness of 0.023 cm and a gas permeability per 1 cm thickness of 8.8cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.116 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 9

A filter was prepared in the same manner as in Example 1, except that asa third filter element eight sheets of nonwoven fabric, each having athickness of 0.023 cm and a gas permeability per 1 cm thickness of 8.8cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.185 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 10

A filter was prepared in the same manner as in Example 1, except that asa third filter element two sheets of nonwoven fabric, each having athickness of 0.053 cm and a gas permeability per 1 cm thickness of 9.6cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.106 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 11

A filter was prepared in the same manner as in Example 1, except that asa third filter element 10 sheets of polyester screen, each having athickness of 0.009 cm and a gas permeability per 1 cm thickness of 8.4cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.090 cm. The recovery time, the amount of blood loss, and theseparation strength were determined. The results are shown in Table 1.

Example 12

A filter was prepared in the same manner as in Example 1, except that asa third filter element four sheets of polyester screen, each having athickness of 0.030 cm and a gas permeability per 1 cm thickness of 28.8cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.120 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 13

A filter was prepared in the same manner as in Example 1, except that asa third filter element three sheets of polyester screen, each having athickness of 0.038 cm and a gas permeability per 1 cm thickness of 36.5cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.114 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 14

A filter was prepared in the same manner as in Example 1, except that asa third filter element five sheets of polyester screen, each having athickness of 0.038 cm and a gas permeability per 1 cm thickness of 36.5cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.190 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 1.

Example 15

A filter shown in FIG. 2 was prepared in the same manner as in Example1, except for the possession of a sheet-like frame and the featuresdescribed below. The recovery time, the amount of blood loss, andseparation strength were determined. The materials for the inlet portside container and outlet port side container and the filter elementwere prepared, in the same manner as in Example 1. The polyvinylchloride resin sheet (n) having the same external dimension as the inletport side container and the outlet port side container was used as thematerial for the outlet port side sheet-like frame, of which the insidearea was cut out leaving a frame with a width of 3 mm inside the firstseal zone (f) The inlet port side sheet-like frame (o) was provided witha frame with a width of 3 mm, on both the inside and outside of thefirst seal zone (f). A filter element was disposed between the outletport side sheet-like frame materials and the inlet port side sheet-likeframe materials. The first seal zone was formed by high frequencywelding. The outlet port side sheet-like frame was covered with thematerial for the outlet port side container and the inlet port sidesheet-like frame was covered with the material for the inlet port sidecontainer. Then, the second seal zone was formed by high frequencywelding in the same manner as in Example 1. The materials of thecontainer and the sheet-like frame extruding outside the second sealzone were cut out. The results are shown in Table 1.

TABLE 1 Third element Recov- Amount of Separation Exam- Gas permeabilityThickness ery time blood loss strength ple (cc/cm²/sec) (cm) (min) (ml)(N/mm) 1 4.5 0.114 4.7 27.3 3.2 2 4.5 0.057 8.1 25.8 3.0 3 4.5 0.171 5.428.1 3.1 4 4.5 0.228 5.6 28.9 2.9 5 3.2 0.088 6.7 26.0 2.2 6 3.8 0.1056.3 27.1 2.2 7 8.8 0.046 6.9 26.9 2.5 8 8.8 0.116 5.7 28.3 2.7 9 8.80.185 4.9 29.7 2.6 10 9.6 0.106 5.4 28.3 2.0 11 8.4 0.090 6.7 27.9 2.612 28.8 0.120 5.5 28.0 1.8 13 36.5 0.114 5.3 28.4 2.4 14 36.5 0.190 5.228.6 2.2 15 4.5 0.114 4.8 27.4 3.2

Comparative Example 1

A filter was prepared in the same manner as in Example 1 except that thethird filter element was not used. The recovery time, the amount ofblood loss, and separation strength were determined. The results areshown in Table 2.

Comparative Example 2

A filter was prepared in the same manner as in Example 1 except that asa third filter element one sheet of nonwoven fabric having a thicknessof 0.019 cm and a gas permeability per 1 cm thickness of 4.5 cc/cm²/secwas laminated. The recovery time, the amount of blood loss, and theseparation strength were determined. The results are shown in Table 2.

Comparative Example 3

A filter was prepared in the same manner as in Example 1, except that asa third filter element two sheets of nonwoven fabric, each having athickness of 0.019 cm and a gas permeability per 1 cm thickness of 4.5cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.038 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 2.

Comparative Example 4

A filter was prepared in the same manner as in Example 1, except that asa third filter element 15 sheets of nonwoven fabric, each having athickness of 0.019 cm and a gas permeability per 1 cm thickness of 4.5cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.285 cm. The recovery time , the amount of blood loss, andseparation strength were determined. The results are shown in Table 2.

Comparative Example 5

A filter was prepared in the same manner as in Example 1, except that asa third filter element one sheet of nonwoven fabric having a thicknessof 0.023 cm and a gas permeability per 1 cm thickness of 8.8 cc/cm²/secwas laminated. The recovery time, the amount of blood loss, and theseparation strength were determined. The results are shown in Table 2.

Comparative Example 6

A filter was prepared in the same manner as in Example 1, except that asa third filter element 12 sheets of nonwoven fabric, each having athickness of 0.023 cm and a gas permeability per 1 cm thickness of 8.8cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.276 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 2.

Comparative Example 7

A filter was prepared in the same manner as in Example 1, except that asa third filter element one sheet of nonwoven fabric having a thicknessof 0.044 cm and a gas permeability per 1 cm thickness of 2.2 cc/cm²/secwas laminated. The recovery time, the amount of blood loss, and theseparation strength were determined. The results are shown in Table 2.

Comparative Example 8

A filter was prepared in the same manner as in Example 1, except that asa third filter element two sheets of nonwoven fabric, each having athickness of 0.044 cm and a gas permeability per 1 cm thickness of 2.2cc/cm²/sec, were laminated to obtain a laminated sheet with a thicknessof 0.088 cm. The recovery time, the amount of blood loss, and separationstrength were determined. The results are shown in Table 2.

Comparative Example 9

A filter was prepared in the same manner as in Example 1, except that asa third filter element two sheets of nonwoven fabric having a thicknessof 0.042 cm and a gas permeability per 1 cm thickness of 0.038cc/cm²/sec were laminated to obtain a laminated sheet with a totalthickness of 0.042 cm. The recovery time, the amount of blood loss, andthe separation strength were determined. The results are shown in Table2.

Comparative Example 10

A filter was prepared in the same manner as in Example 1, except that asa third filter element three sheets of nonwoven fabric, each having athickness of 0.042 cm and a gas permeability per 1 cm thickness of 0.038cc/cm²/sec were laminated to obtain a laminated sheet with a totalthickness of 0.126 cm. The recovery time, the amount of blood loss, andthe separation strength were determined. The results are shown in Table2.

Comparative Example 11

A filter was prepared in the same manner as in Example 1, except thatinstead of the third filter element five sheets of nonwoven fabric, eachhaving a thickness of 0.042 cm and a gas permeability per 1 cm thicknessof 0.038 cc/cm²/sec were laminated to obtain a laminated sheet with atotal thickness of 0.208 cm. The recovery time, the amount of bloodloss, and the separation strength were determined. The results are shownin Table 2.

Comparative Example 12

A filter was prepared in the same manner as in Example 1, except thatone sheet of polyolefin screen, with one side of the opening of 2.8 mm,a fiber diameter of 500 μm, and an opening ratio of 77%, was laminatedinstead of a third filter element to provide a thickness of 0.090 cm.The recovery time, the amount of blood loss, and separation strengthwere determined. The gas permeability of the screen per 1 cm thicknesscould not be measured because the value was too large to determine.Based on the number of laminated sheets and the measured area of thetest specimen, the gas permeability estimated to be larger than 100cc/cm²/sec. The results own in Table 2.

TABLE 2 Third element Amount of Separation Comparative Gas permeabilityThickness Recovery blood loss strength Example (cc/cm²/sec) (cm) time(min) (ml) (N/mm) 1 — 0 17.4 24.5 0.9 2 4.5 0.019 13.9 25.0 1.2 3 4.50.038 11.1 25.3 1.4 4 4.5 0.285 6.0 30.1 1.2 5 8.8 0.023 10.5 26.4 1.0 68.8 0.276 5.2 30.8 1.3 7 2.2 0.044 12.7 25.5 2.2 8 2.2 0.088 12.5 26.32.0 9 0.38 0.042 13.4 29.0 0.9 10 0.38 0.126 16.1 31.0 1.0 11 0.38 0.20818.7 33.8 0.9 12 >100 0.090 5.1 28.6 0.9

Example 16

An inlet port side container material (b) having an inlet port (a) andan outlet port side container material (d) having an outlet port (e),each having a dimension of 120 mm×100 mm, as shown in FIG. 1, wereprepared by combining a blood inlet port (a) and a blood outlet port(e), each made of a polyvinyl chloride resin formed by injectionmolding, with sheets (b) and (d) of soft polyvinyl chloride resin, eachhaving a hole at the location of adherence, by means of high frequencywelding. A laminate of the following sheets of nonwoven polyester fabricwas used as the filter element (c). Four sheets of nonwoven fabric (1)with an average fiber diameter of 12 μm and a density of 30 g/m² wereused as the first filter element. As the second filter element, a total27 sheets of nonwoven fabric consisting of one sheet of nonwoven fabric(2) with an average fiber diameter of 1.7 μm and a density of 66 g/m²,25 sheets of nonwoven fabric (3) with an average fiber diameter of 1.2μm and a density of 40 g/m², and one sheet of nonwoven fabric (2) werelaminated in that order. Then, one sheet of the nonwoven fabric (1) waslaminated as the third filter element, with the total of 32 sheets beinglaminated. The gas permeability per 1 cm thickness of the third filterelement was 4.5 cc/cm²/sec and the thickness was 0.019 cm. The laminatedfilter element was cut into a rectangle of 85 mm×68 mm to be used as thefilter element (c). The flexible container materials (b, d) and thefilter element (c) were layered as shown in FIG. 1, and welded by highfrequency welding to form the first seal zone (f) with a length of 3 mm.No second seal zone was formed to reduce the time required for the test.15 filters prepared in this manner was divided into three groups. Thethickness of the composite material layer, separation strength, andfracture time were determined using five filters of each group. Theaverage of the results obtained for five filters is shown in Table 3.

Example 17

A filter was prepared in the same manner as in Example 1, except forusing two sheets of nonwoven fabric (1) as the third filter element. Thesame test as in Example 16 was carried out. The average of the resultsobtained for five filters is shown in Table 3. The gas permeability per1 cm thickness of the third filter element was 4.5 cc/cm²/sec and thethickness was 0.038 cm.

Example 18

A filter was prepared in the same manner as in Example 1, except forusing four sheets of nonwoven fabric (1) as the third filter element.The same test as in Example 16 was carried out. The average of theresults obtained for five filters is shown in Table 3. The gaspermeability per 1 cm thickness of the third filter element was 4.5cc/cm²/sec and the thickness was 0.076 cm.

Example 19

A filter was prepared in the same manner as in Example 1, except forusing six sheets of nonwoven fabric (1) as the third filter element. Thesame test as in Example 16 was carried out. The average of the resultsobtained for five filters is shown in Table 3. The gas permeability per1 cm thickness of the third filter element was 4.5 cc/cm²/sec and thethickness was 0.114 cm.

Example 20

A filter was prepared in the same manner as in Example 1, except forusing eight sheets of nonwoven fabric (1) as the third filter element.The same test as in Example 16 was carried out. The average of theresults obtained for five filters is shown in Table 3. The gaspermeability per 1 cm thickness of the third filter element was 4.5cc/cm²/sec and the thickness was 0.0152 cm.

Example 21

A filter was prepared in the same manner as in Example 1, except forusing four sheets of nonwoven fabric (1) as the third filter element andincreasing the number of sheets of nonwoven fabric (3) for the secondfilter element to 32 sheets. The same test as in Example 1 was carriedout. The average of the results obtained for five filters is shown inTable 3. The gas permeability per 1 cm thickness of the third filterelement was 4.5 cc/cm²/sec and the thickness was 0.076 cm.

Example 22

Four sheets of the nonwoven fabric (1) were laminated as the firstfilter element, 27 sheets in total consisting of one sheet of nonwovenfabric (2), 25 sheets of nonwoven fabric (3), and one sheet of nonwovenfabric (2) were laminated as the second filter element, and four sheetsof the nonwoven fabric (1) were laminated as the third filter element,with the total of 35 sheets being laminated. The gas permeability per 1cm thickness of the third filter element was 4.5 cc/cm²/sec and thethickness was 0.076 cm. The laminated filter element was cut into arectangle of 85 mm×68 mm to be used as the filter element. The filterelement was sandwiched between an inlet port side sheet-like frame thatis cut into a frame-shape with an external dimension of 85 mm×68 mm andinternal dimension of 69 mm×52 mm and an outlet port side sheet-likeframe that is cut into a frame-shape with an external dimension of 120mm×100 mm and internal dimension of 69 mm×52 mm. The layered sheet-likeframes were attached to the filter element by high frequency welding toprovide a first seal zone with a width of 3 mm. Then, the outlet portside sheet-like frame was placed between an inlet port side containermaterial (120 mm×100 mm) with an inlet port and an outlet port sidecontainer material (120 mm×100 mm) with an outlet port and welded byhigh frequency welding to provide a second seal zone with an internaldimension of 91 mm×74 mm and a width of 3 mm. 15 filters prepared inthis manner was divided into three groups. The thickness of thecomposite material layer, separation strength, and fracture time weredetermined for five filters of each group. The average of the resultsobtained for five filters is shown in Table 3.

TABLE 3 Composite material layer Thickness of on Thickness of onSeparation Fracture Example inlet port side (mm) outlet port side (mm)strength (N/mm) time (sec) 16 0.183 0.182 2.61 1024 17 0.282 0.183 2.58978 18 0.278 0.241 2.88 1545 19 0.287 0.256 2.74 1285 20 0.278 0.3162.71 1315 21 0.293 0.324 3.05 2064 22 0.355 0.355 2.21 673

Comparative Example 13

A filter was prepared without using a third filter element, withoutusing the nonwoven fabric (1) on the outlet port side, and employinghigh frequency welding conditions for providing the composite materiallayer with a thickness of 0.1 mm or less. The method of Example 1 wasfollowed for all other filter preparation conditions. Then, the sametests as in Example 1 were-carried out. The average of the resultsobtained for five filters is shown in Table 4.

Comparative Example 14

A commercially available frame welding type filter was obtained tomeasure the thickness of composite material layer, theseparation-breaking strength, and the fracture time. This filter hadsheet-like frames disposed on both the inlet port side and the outletport side as shown in FIG. 2, with only the outlet port side sheet-likeframe being joined with the container to form a second seal zone. Thethickness of the composite material layer in the outlet port sidesheet-like frame forming the second seal zone was less than 0.15 mm. Asdescribed in connection with the method of measurement, to make itpossible to carry out these tests, a sheet of soft polyvinyl chloride,which is the same material as the sheet-like frame, was caused to adhereto the sheet-like frame prior to the measurement of theseparation-breaking strength and the fracture time. The results areshown in Table 4.

TABLE 4 Composite material layer Separation- Comparative Thickness of oninlet Thickness of on outlet breaking strength Fracture Example portside (mm) port side (mm) (N/mm) time (sec) 13 0.243 0.004 1.57 8 140.250 0.132 0.77 10

INDUSTRIAL APPLICABILITY

As described above, a flexible blood processing filter, in which theblood flow may not be affected when the filter element is caused toadhere to the outlet port side container due to the positive pressure onthe inlet port side or the negative pressure on the outlet port sideduring filtration operation, can be provided by selecting the gaspermeability and the thickness of the third filter element. In addition,a flexible blood processing filter with superior pressure resistance,separation resistance, and sufficient strength against the pressureduring filtration or the stress during centrifugation can be provided byforming a composite material layer with a thickness of 0.15-0.4 mm.

1. A blood processing filter comprising a flexible container, which hasa blood inlet port and a blood outlet port, and a sheet-like filterelement for removing undesirable components from blood, wherein, theblood inlet port is separated from the outlet port by the filterelement, a first seal zone is formed by integrating a section near aperiphery of the sheet-like filter element with the flexible containerover an entire circumference of the flexible container, a second sealzone is formed by integrating a blood inlet port side section of theflexible container with a blood outlet port side section of the flexiblecontainer over an entire outside circumference of the first seal zone,an unsealed zone disposed between the first seal zone and the secondseal zone, and a cross-section of the first seal zone comprises at leastfive layers from the blood inlet port side to the blood outlet portside, said five layers consist of a layer consisting only of a bloodinlet port side flexible container material, a blood inlet port sidecomposite material layer wherein the blood inlet port side flexiblecontainer material is mixed with a filter element material, a moltencontainer material invading fiber voids of the filter element and thefibers being embedded by the material of the container, a layerconsisting only of molten filter element material, a blood outlet portside composite material layer wherein a blood outlet port side flexiblecontainer material is mixed with the filter element material, the moltencontainer material invading the fiber voids of the filter element andthe fibers being embedded by the material of the container, and a layerconsisting only of a blood outlet port side flexible container material,wherein both the blood inlet port side composite material layer and theblood outlet port side composite material layer have a thickness between0.15 mm and 0.4 mm.
 2. The blood processing filter according to claim 1,wherein the filter element comprises a first filter element for removingaggregate from blood and a second filter element arranged downstream ofthe first filter element to remove leukocytes.
 3. The blood processingfilter according to claim 1, wherein the filter element comprises athird filter element disposed between the second filter element and theblood outlet port side of the flexible container for preventing adhesionof the blood outlet port side of the flexible container to the secondfilter element.
 4. The blood processing filter according to claim 2,wherein the blood inlet port side composite material layer contains thematerial of the blood inlet port side of the flexible container or asheet-like frame and the first filter element as main components.
 5. Theblood processing filter according to claim 3, wherein the blood outletport side composite material layer contains the material of the bloodoutlet port side of the flexible container and the third filter elementas main components.
 6. The blood processing filter according to claim 3,wherein the third filter element has a gas permeability per 1 cmthickness of 3-40 cc/cm²/sec and a thickness of 0.04-0.25 cm.
 7. Theblood processing filter according to claim 1, wherein the flexiblecontainer is formed from a sheet-like formed material.
 8. The bloodprocessing filter according to claim 1, wherein the flexible containeris formed from a cylindrical formed material.
 9. The blood processingfilter according to claim 1, wherein the blood inlet port and bloodoutlet port made from formed parts are liquid-tightly joined with theflexible container.
 10. The blood processing filter according to claim1, wherein the flexible container is formed from soft polyvinylchloride.
 11. The blood processing filter according to claim 1, whereinthe blood inlet port and blood outlet port are formed from softpolyvinyl chloride.
 12. The blood processing filter according to claim1, wherein the flexible container is formed from polyolefin.
 13. Theblood processing filter according to claim 12, wherein the blood inletport and blood outlet port are formed from polyolefin.
 14. A system forremoving leukocytes from blood, comprising: a centrifuge; and the bloodprocessing filter according to claim 1.